WO2023172862A2 - Technologies de surveillance pour bobines et réseaux d'irm - Google Patents

Technologies de surveillance pour bobines et réseaux d'irm Download PDF

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Publication number
WO2023172862A2
WO2023172862A2 PCT/US2023/063764 US2023063764W WO2023172862A2 WO 2023172862 A2 WO2023172862 A2 WO 2023172862A2 US 2023063764 W US2023063764 W US 2023063764W WO 2023172862 A2 WO2023172862 A2 WO 2023172862A2
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WO
WIPO (PCT)
Prior art keywords
mri
transmit
coil
testing
testing system
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PCT/US2023/063764
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English (en)
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WO2023172862A3 (fr
Inventor
Carl SYNDER
Jay D. Miller
Brandon Lee MAGNAN
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Nortech Systems, Inc.
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Publication of WO2023172862A2 publication Critical patent/WO2023172862A2/fr
Publication of WO2023172862A3 publication Critical patent/WO2023172862A3/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
    • G01R33/341—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils
    • G01R33/3415—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils comprising arrays of sub-coils, i.e. phased-array coils with flexible receiver channels

Definitions

  • the disclosed implementations relate generally to testing magnetic resonance imaging (MRI) coils in MRI systems, and specifically to testing the resonant frequency of the MRI coils, the detuning circuit of MRI systems, the inductive coupling between coils within coil arrays, the temperature of individual coils and array cables of MRI systems.
  • MRI magnetic resonance imaging
  • a fixture that can test MRI coils or an array of MRI coils.
  • This fixture may be used outside of the magnet room prior to patient scanning.
  • Implementations of a fixture as described herein can test the integrity of the MRI coil or array of MRI coils by checking each individual coil’s resonant frequency, checking each individual coil’s nse/ringdown time, and checking the inductive coupling between coils within an array.
  • the fixture may send coil data to a cloud database where it can be analyzed and aggregated with data from other coils, which can be used to predict, e.g., with artificial intelligence, how long an MRI coil has before it breaks.
  • an integrated system that can determine the health and safety of a receiver coil or array in an MRI system by continuously monitoring the MRI coil or array throughout a patient scan.
  • Implementations of an integrated system as described herein can test, during clinical use of an MRI system, the integrity of the MRI coil or array of MRI coils by checking each individual coil’s resonant frequency, checking each individual coil’s rise/ringdown time, and checking the temperature of each individual coil within the array as well as the temperature of the array cable attached to a table mounted connector. If an MRI coil’s resonant frequency is too far from the known Larmor frequency, the ring-up or ring-down time is too long, or the temperature of the MRI coil or cable is too high, the system outputs a warning.
  • Figure 1 is a block diagram of an MRI coil testing system in accordance with some implementations.
  • Figure 2 is a block diagram of a transmit unit of the MRI coil testing system of Figure 1, in accordance with some implementations.
  • Figure 3 is a block diagram of a receive unit of the MRI coil testing system of Figure 1, in accordance with some implementations.
  • Figure 4 is a schematic of a system coupled to an array of MRI coils, in accordance with some implementations.
  • Figure 5 is a schematic of an alternate system coupled to an array of MRI coils, in accordance with some implementations.
  • Figure 6 is a schematic of an alternate system coupled to an array of MRI coils, in accordance with some implementations.
  • Figure 7 is a schematic of an alternative MRI coil system in accordance with some implementations.
  • Figure 8 is a block diagram of an MRI coil testing system in accordance with some implementations.
  • Figure 9 is a block diagram of a receive unit of the MRI coil testing system of Figure 8, in accordance with some implementations.
  • Figure 10 is a schematic of a system coupled to an array of MRI coils, in accordance with some implementations.
  • Figure 11 is a schematic of an alternate system coupled to an array of MRI coils, in accordance with some implementations.
  • Figure 12 is a schematic of an alternate system coupled to an array of MRI coils, in accordance with some implementations.
  • Figure 13 is a schematic of an alternative MRI coil system in accordance with some implementations.
  • Figures 14 is a schematic of a temperature probe arrangement with separate processors in accordance with some implementations.
  • Figure 15 is a schematic of a temperature probe arrangement with a single processor in accordance with some implementations.
  • Figure 16 is a schematic of a temperature probe arrangement in a cable in accordance with some implementations.
  • Figure 17 is a schematic of an alternative MRI coil system with additional processors in accordance with some implementations.
  • the term “if’ is, optionally, construed to mean “when” or “upon” or “in response to determining” or “in response to detecting” or “in accordance with a determination that,” depending on the context.
  • the phrase “if it is determined” or “if [a stated condition or event] is detected” is, optionally, construed to mean “upon determining” or “in response to determining” or “upon detecting [the stated condition or event]” or “in response to detecting [the stated condition or event]” or “in accordance with a determination that [a stated condition or event] is detected,” depending on the context.
  • Testing system 100 includes a transmit subsystem 10, a receiver subsystem 11, and a connector subsystem 12.
  • An MRI system is operatively (physically and/or communicatively) coupled to transmit subsystem 10, receiver subsystem 11, and connector subsystem 12.
  • MRI system 2 is separately operatively coupled to transmit subsystem 10, receiver subsystem 11 and connector subsystem 12.
  • MRI system 2 contains an MRI coil 20, which may be coupled to other electronic components (e g., inductors 201, capacitors 202, and a diode 203), the specifics of which are outside the scope of this disclosure.
  • Transmit subsystem 10 may contain a transmit antenna 102 and a signal generator 101.
  • the signal generator 101 of transmit subsystem 10 may also include frequency generator 1010 and swept frequency generator 1011, which are both fed into multiplexor 1012. The output of multiplexor 1012 is fed to bandpass filter 1013, which is then transmitted by transmit antenna 102.
  • transmit antenna 102 may be communicatively and/or physically coupled to MRI coil 20 (e.g., coupled to a capacitor 202 of MRI coil 20), to facilitate testing of MRI coil 20.
  • coil 20 is designed to resonate at a resonant frequency referred to as the Larmor frequency.
  • signal generator 101 may be configured to generate a plurality of transmit signals at a plurality of transmit signal frequencies within a transmit frequency band close to the Larmor Frequency.
  • frequency generator 1010 and swept frequency generator 1011 may both generate signals, which are multiplexed up to the Larmor frequency or the other adjacent testing frequencies by multiplexor 1012 and then filtered by bandpass filter 1013. Once each signal is ready, the transmit antenna 102 may transmit the signal to MRI coil 20 via the coupling of transmit antenna 102 to capacitor 202 of MRI coil 20. Coil 20 will then absorb energy from each of the signals transmitted by transmit antenna 102 and generate a frequency response.
  • one or more of bandpass filter 1013, multiplexor 1012, frequency generator 1010, and swept frequency generator 1011 may be removed from transmit subsystem 10.
  • the components of transmit subsystem 10 are just one example implementation among many; components may be removed, added, and/or substituted as long as the transmit subsystem 10 is configured to transmit signals as described herein.
  • Receive subsystem 11 may contain a receiver antenna 110, a receiver unit 111 and an external antenna 112.
  • receiver unit 111 may include a preamplifier 1 110, a bandpass filter 1 11 1 , a frequency generator 1 1 12, a multiplexor 1 1 13, an analog to digital converter 1114 and a processor 1115.
  • Analog to digital converter 1114 and processor 1115 may be operatively coupled to external antenna 112.
  • receiver antenna 110 may also be communicatively and/or physically coupled to MRI coil 20 (e g., coupled to capacitor 202 of MRI coil 20). However, in one aspect of the disclosure, transmit antenna 102 and receiver antenna 110 are both coupled to capacitor 202 of MRI coil 20 but are not coupled to each other.
  • preamplifier 1110 bandpass filter 1111, frequency generator 1112, multiplexor 1113, analog to digital converter 1114, and processor 1115 may be removed from receive subsystem 11.
  • the components of receive subsystem 11 are just one example implementation among many; components may be removed, added, and/or substituted as long as the receive subsystem 11 is configured to transmit signals as described herein.
  • transmitter subsystem 11 To test the MRI coil’s resonance, transmitter subsystem 11 generates a signal that sweeps across a frequency band close to (e.g., within 50% of) and on the Larmor frequency.
  • the signal is broadcasted by the transmit antenna 112 which is also coupled to the MRI coil 20.
  • the receiver antenna 110 which is also coupled to the MRI coil 20, receives the amplitude of the MRI coil’s frequency response. As the transmit frequency gets closer to the Larmor frequency, the amplitude of the signal received at the receiver antenna 110 should also increase. If the received signal (received at receiver antenna 110) is not maximum at the Larmor frequency, then the MRI coil 20 is not resonant (not resonant as designed or otherwise intended), and is therefore broken.
  • receive antenna 110 receives each frequency response, which may include an inductive voltage.
  • Receive antenna 110 then sends the received frequency response signal to the receiver unit 111, which puts the signal through preamplifier 1110 and then through bandpass filter 1111.
  • Multiplexor 1113 and frequency generator 1112 may then multiplex the received signal to a lower frequency.
  • the lower frequency signal is then converted to digital data by analog to digital converter 1114, and the digital data is sent to processor 1115, which analyzes the signal data to determine whether the frequency response signal with the highest amplitude is the frequency response signal that corresponds to the transmit signal whose frequency was the Larmor frequency.
  • Processor 1115 may be configured to provide immediate feedback to the end user, and may also be configured to transmit the received frequency response signal data to external antenna 112.
  • External antenna 112 may be external to the system or it may be internal to the system, but it is configured to transmit the data externally.
  • external antenna 112 will send the received signal to a cloud-based server 3 that contains coil testing database 30.
  • Server 3 may then perform more complex statistical algorithms, which may include artificial intelligence (Al), which may analyze the data, informed by data from other MRI coils, to provide predictive trends for future coil failure.
  • Al artificial intelligence
  • MRI systems such as MRI system 2 may contain receive-only coils and arrays, which need to be detuned or not resonant while the body coil is transmitting. This is traditionally done by adding a PIN diode, although some MRI systems may use MEMS or other switches, and an inductor into the MRI coil circuit.
  • the PIN diode When the MRI coil is transmitting during an imaging task, the PIN diode is energized, which creates an LC band reject filter at the Larmor frequency that prevents the MRI coil from resonating at the Larmor frequency.
  • the I region of a PIN diode and MEMS switches may degrade.
  • receive-only coils e.g., coil 20
  • coil arrays may need to be detuned (not resonant) while the body coil is transmitting. This may be done by adding a PIN diode (other methods may use MEMS or other switches) and inductor into the MRI coil circuitry. During transmit, the PIN diode is energized, which creates an LC band reject filter at the Larmor frequency. This prevents the MRI coil from resonating at the Larmor frequency. However, over time the I region of the PIN diode and MEMS switches start degrading.
  • the transmitter in the test fixture continuously transmits a signal at the Larmor frequency while the DC switching supply rapidly switches +/- 10VDC (or between any other voltage rails greater than or less than 10VDC), through the connector, to the PIN diode or MEMS switch.
  • the DC supply tunes and detunes the MRI coil 20 on and off of the Larmor frequency.
  • the receiver on the test fixture measures the amplitude of the receiver coil in the time domain. If the MRI coil 20 does not tune and detune fast enough, the MRI coil is broken.
  • the receiver sends the amplitude data to a cloud-based database for additional analysis.
  • testing system 100 may be used to test the detuning circuit of an MRI system, using receiver subsystem 11 and connector subsystem 12.
  • Connector subsystem 12 may include a magnetic resonance / radio frequency (MR/RF) connector 120 and a direct current (DC) switching supply 121.
  • Connector 120 may be designed to be coupled to an MR/RF connector 21 of MRI system 2
  • DC switching supply 121 connectors may be designed to be coupled to DC switching supply 204 connectors.
  • MRI system 2 may also contain a detuning circuit 22 which may include a tune and match network 220, a phase shifting network 221, and a preamplifier 222.
  • the transmit subsystem continuously transmits a signal at the Larmor frequency while the DC switching supply is rapidly switched between positive and negative voltage rails (e.g., +/- 10VDC, or any other voltage rails greater than or less than 10VDC).
  • Diode 203 may be a PIN diode. In other MRI systems, the functions of diode 203 may be performed instead by a MEMS switch.
  • the switching of DC switching supply 204 of MRI coil 20 causes the MRI to tune and detune while the transmit subsystem is transmitting the signal at the Larmor frequency.
  • receive antenna 110 then sends the received signal to receiver unit 111, which puts the signal through preamplifier 1110 and then through bandpass filter 1111.
  • Multiplexor 1113 and frequency generator 1112 may then multiplex the received signal to a lower frequency.
  • the lower frequency signal is then converted to digital data by analog to digital converter 1114, and the digital data is sent to processor 1115.
  • Receiver subsystem 11 measures the amplitude of the received response signal in the time domain, which signals how quickly the coil tunes and detunes. If coil 20 does not tune and detune fast enough (the amplitude does not rise and fall faster than a threshold), coil 20 or detuning circuit 22 may be broken.
  • Receiver unit 111 may then send the data to cloud-based server 3 for additional analysis, which may include predictive failure analysis for detuning circuit 22 or coil 20, which may be based on data from similar coils or detuning circuits, including which rise and fall numbers predict failure, and how soon.
  • additional analysis may include predictive failure analysis for detuning circuit 22 or coil 20, which may be based on data from similar coils or detuning circuits, including which rise and fall numbers predict failure, and how soon.
  • FIG. 4, 5, 6, 7A and 7B block diagrams of the present disclosure, as deployed in an MRI system 2 with an array of MRI coils 20 are shown.
  • Array coil systems may be used in MRI applications, because an individual coil may not provide enough coverage of the anatomy of the patient being scanned. By combining multiple small coils into large arrays, it is possible to obtain a high signal to noise ratio of a small cable and a large field of view.
  • an array of MRI coils may be a switchable array, wherein different individual coils, or different sub-arrays, could be switched on and off to scan different areas of the patient’s body.
  • an array of MRI coils may be a phased array.
  • an array of MRI coils may be a parallel array. Some coil arrays may be divided into segments and/or into channels.
  • a testing system in accordance with Figure 1 may be useful in an MRI system featuring an array of MRI coils, to diagnose the resonant frequency of individual coils in the array or to diagnose a detuning circuit to ensure that coils rise and fall within acceptable time intervals.
  • Figure 4 shows an array of twelve coils 20 within a single MRI system 2.
  • Testing system 100 as shown in Figure 4 may have a single transmit subsystem 10 and a single receive subsystem 11.
  • the single transmit subsystem 10 may have a single transmit antenna 102 and a single signal generator 101.
  • the single transmit antenna may be operatively coupled to all twelve of the MRI coils 20, and may be configured to direct a signal generated by the signal generator 101 to any of the MRI coils 20.
  • Receive subsystem 11 may contain a single receive antenna 110 and a single receiver unit 111.
  • Receive antenna 110 may receive frequency responses as described above, for each of the 12 coils 20 in the array of MRI coils. Because it is coupled to the twelve coils, receiver subsystem 11 in Figure 4 may be able to identify which of the twelve coils is generating a frequency response signal, so that it is able to accurately create and analyze data relating to which coil 20 of the array may be diagnosed as failing or predicted to fail.
  • an array need not be limited to twelve coils 20, and can be more or fewer coils 20. Persons having skill in the art will realize that different arrangements of MRI coils 20 in an array may be used, and that the arrangement shown is exemplary only.
  • FIG. 5 an alternate arrangement, to that of Figure 4, for use with arrays, is shown.
  • a twelve-coil array of MRI coils 20 is shown, similar to the array of Figure 4.
  • Also shown in Figure 5 are four receive subsystems 11, consisting of four receive antennas 110 and four receiver units 111.
  • the transmit subsystems 10 and receive subsystems 11 may be configured such that each one of transmit subsystem 10 and each receive subsystem 11 may be coupled to a segment or channel of MRI coils 20 or some other subset of the array.
  • each transmit subsystem 10 and each receive subsystem 11 may be coupled to three coils 20, such that a set of four transmit subsystems 10 and four receive subsystems 11 can test twelve coils 20.
  • the ratio of transmit subsystems 10 and receiver subsystems 11 to MRI coils 20 need not be 1 :3 or any specific ratio, and that different transmit subsystems 10 and receiver subsystems 11 in the same testing system 100 may be coupled to different numbers of MRI coils 20 as compared to other transmit subsystems 10 or receiver subsystems 11 in the same testing system 100.
  • FIG. 6 an alternate arrangement to that of Figures. 4 and 5 is shown with respect to an array of twelve coils 20.
  • switch 13 allows a single signal generator 101 to switch between being coupled to each of the four transmit antennas 102.
  • Switch 13 also allows a single receiver unit 111 to switch between being coupled to each of the four receive antennas 110. This way, each of the antennas can be coupled to fewer of the MRI coils 20 of the array, but the amount of circuitry for signal generator 101 and receiver unit 111 can be minimized.
  • the ratio of antennas 102 and 110 to MRI coil 20 need not be 1 :3 or any specific ratio.
  • the switched configuration of Figure 6 is not limited to one single signal generator 101 and one single receiver unit 111, and that multiple signal generator 101 may exist in a system where there are more transmit antennas 102 than there are signal generators 101, without the specific ratio being 1:4 as shown in Figure 6.
  • FIGS 4 through 6 show a planar array of twelve coils 20, which has the MRI coils in the array in a single plane.
  • testing system 100 may also be deployed in a volume coil array, which are used in MRI tube systems that surround patients, e.g. in a cylindrical shape, while they are being imaged.
  • a schematic of the testing system 100 as deployed in a volume coil array is shown in Figure 7.
  • the test fixture tests inductive coupling between MRI coils within an array of MRI coils. Inductive coupling between receiver coils significantly reduces the signal to noise ratio in an image.
  • the test fixture energizes all coils and their preamps (e.g., by applying a DC voltage) and collects noise-only data. Neither the transmitter nor the receiver is used in this test. The signal from each coil should be uncorrelated (e.g., uncorrelated Gaussian noise). If two coils within the array have significantly correlated noise, the test system may output an inductive coupling warning.
  • DC switching supply 121 may supply power to DC switching supply 204 to energize all of the MRI coils 20 in the array, or all of the MRI coils in a particular segment or subset of the array.
  • the signal from each coil should be Gaussian noise, uncorrelated to the noise produced by another coil in the array. If two coils within the array have significantly correlated noise (e.g., noise having a level of correlation above a threshold), the test system may output an inductive coupling warning (e.g., to warn a radiology technologist operating the MRI system).
  • testing system 800 Figure 8-17
  • Figure 8-17 an integrated testing system that can be operated during clinical use of the MRI system.
  • the MRI coil 20, tune and match network 220, phase-shifting network 221, preamp 222, MRI signal line, DC control lines, and MR/RF connector 21 in testing system 800 correspond to those described above with reference to testing system 100, and are not further described here for purposes of brevity and so as no the descriptions above equally apply to the corresponding components in testing system 800.
  • testing system 800 there are two main differences compared to testing system 100.
  • the receiver system probe 802 and receiver unit 804 in system 800 are embedded inside or otherwise internally coupled to the MRI coil 20 and may therefore make measurements during an MRI scan in a clinical setting.
  • the receiver antenna 110 and receiver unit 111 in system 100 may be coupled to an external testing fixture or jig for use outside the MRI scanner room prior to a scan. Since the probes and receiver unit in testing fixture 800 are inside (or otherwise integrated with or coupled to) the MRI coil, the transmit subsystem 10 ( Figure 1) is unnecessary and is therefore not part of system 800.
  • the transmit signals described above with reference to system 100 may be applied internally by virtue of running the MRI system (e.g., by a controller and/or signal generator of the MRI system), and the receive signals described above with reference to system 100 are directly received from the MRI coil in system 800.
  • the MRI coil circuitry 820 of system 800 may run normally (e.g., during clinical scans) while probe 802 senses and receiver unit 804 determines the natural resonant frequency of the coil 20.
  • testing system 800 additionally includes temperature sensors 812 (e.g., fiber optic temperature sensors).
  • the temperature sensors 812 also referred to as temperature probes 812 are added to the MR1 coil and/or the cable. This provides additional safety specifications, alerting the user if the coil is heating up to unsafe levels (e.g., past IEC regulatory standards).
  • System 800 is a complete safety test fixture that determines the health and safety of a receiver coil or array.
  • System 800 includes a receiver subsystem 801 and a temperature subsystem 811.
  • Receiver subsystem 801 in system 800 corresponds to receiver subsystem 11 in testing system 100. However, since receiver subsystem 801 in system 800 is located inside the MRI system and directly coupled to the coil, it may continuously monitor the coil or array throughout a patient scan. More specifically, receiver subsystem 801 includes a probe 802 (e.g., an H-field probe or the like), a receiver unit 804, and a processor (814 ( Figure 8), 1115 (Figure 9), and/or 805 ( Figure 17)) (e.g., a microcontroller or microprocessor).
  • a probe 802 e.g., an H-field probe or the like
  • a processor 814
  • 1115 Figure 9
  • 805 Figure 17
  • Receiver subsystem 801 monitors the resonant (or Earmor) frequency as well as the ring-up and ringdown time (on and off time) for each individual coil within an array (similar to the receiver subsystem of system 100). If the coil’s resonant frequency is too far from the know n Larmor frequency, or if the ring-up or ring-down time is too long, the processor may output a warning (similar to the receiver subsystem of system 100).
  • FIG. 9 is a block diagram of the receive unit 804 of system 800 in accordance with some implementations.
  • the components of the receive unit of system 800 correspond to respective components of the receive unit of system 100, and are not further described here for purposes of brevity.
  • Receive unit 804 may include or otherwise be coupled to an antenna (Bluetooth or Wi-Fi) 112 to send the signal data to a cloud-based server 30 ( Figure 8) for more complex statistical algorithms (Al) to analyze the data to provide predictive trends for coil health (with respect to resonant .
  • Bluetooth Bluetooth or Wi-Fi
  • Figures 10-13 correspond to Figures 4-7, with the difference being lack of transmit subsystem in Figures 10-13 due to system 800 being integrated into the MRI system and not requiring an independent transmit subsystem as described with reference to system 100.
  • a single receive subsystem ( Figure 10) or multiple receive subsystems ( Figure 11) may be used for an array of MRI coils, multiple H-field probes 802 (each corresponding to a different coil 20) may be switched to a single receive unit 804 ( Figure 12), and the coil array may be comprise planar coils ( Figures 10-12) or volume coils ( Figure 13).
  • temperature subsystem 81 1 in system 800 includes a temperature probe 812 (e.g., any ty pe of device that detects and measures hotness and coolness and converts it into an electrical signal) and a processor 814 configured to process the temperature data obtained from the temperature probes.
  • Processor 814 may be the same processor as that used by the receiver subsystem ( Figure 8) or may be a separate processor ( Figure 17).
  • Temperature subsystem 811 monitors the temperature of each individual coil 20 within the array and/or the temperature of the array cable 820 attached to the table mounted connector 830 of the MRI system. If the temperature of a coil 20 or the cable 820 is too high, processor 814 may output a warning.
  • temperature subsystem 811 monitors the internal temperature of the individual coils 20 and cable assembly 820. If processor 814 determines that a monitored temperature exceeds a threshold (e.g., a threshold corresponding to a relevant standard, such as IEC 60601-1, IEC 60601-1-2, or an MITA standard), processor 814 may output a notification, notifying a user to end the current scan immediately. Processor 814 may output a subsequent notification, notify the user when the temperature is safe to scan again.
  • a threshold e.g., a threshold corresponding to a relevant standard, such as IEC 60601-1, IEC 60601-1-2, or an MITA standard
  • a temperature probe 812 may be placed on or near each individual coil 20. Multiple temperature probes 812 may be placed on a single coil (as shown in Figures 14 and 15). Each temperature probe 812 may be coupled to a separate processor 814 ( Figure 14) or to the same processor 814 ( Figure 15). Additionally, multiple temperature probes 812 may be placed inside the cable 820 that is between the coil circuitry 810 and the table connector 830 (as shown in Figure 16). The temperature probes 812 may be set at various intervals along the cable 820. The data from the temperature probes 812 is sent to processor(s) 814.
  • processor(s) 814 may be placed on or near each individual coil 20. Multiple temperature probes 812 may be placed on a single coil (as shown in Figures 14 and 15). Each temperature probe 812 may be coupled to a separate processor 814 ( Figure 14) or to the same processor 814 ( Figure 15). Additionally, multiple temperature probes 812 may be placed inside the cable 820 that is between the coil circuitry 810 and the table connector 830
  • the temperature subsystem 811 may be attached to an antenna 112 (Bluetooth or Wi-Fi) to send the temperature data to a cloud-based server 30 for more complex statistical algorithms (Al) to analyze the data to provide predictive trends for coil heating.
  • Bluetooth Bluetooth or Wi-Fi
  • Al complex statistical algorithms
  • processor 814 may immediately output a warning, notifying the user that temperature is unsafe and out of compliance with the standard. If temperature probe 812 detects temperatures nearing the threshold (e.g., between 41 and 43°C) temperature subsystem 811 may continue to monitor the temperature (e.g., at a higher sample rate), and if temperature probe 812 continues to detect temperatures nearing the threshold for an extended amount of time, processor 814 may output an alert, notifying the user that the temperature is exceeding, or is close to exceeding, the standards and requesting that the user terminate the scan. Processor 814 may also output an alert notifying the user when the temperature is low enough to continue scanning.
  • temperatures nearing the threshold e.g., between 41 and 43°C
  • temperature subsystem 811 may continue to monitor the temperature (e.g., at a higher sample rate)
  • processor 814 may output an alert, notifying the user that the temperature is exceeding, or is close to exceeding, the standards and requesting that the user terminate the scan.
  • Processor 814 may also output an alert notifying the user

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Abstract

Un système de test de bobine d'IRM comprend un sous-système de surveillance de réponse en fréquence et un sous-système de surveillance de température. Le sous-système de surveillance de réponse en fréquence comprend une sonde de réception intégrée conçue pour mesurer chaque fréquence de résonance de bobine individuelle et un temps de gain d'intensité/perte d'intensité, ainsi qu'un processeur configuré pour émettre une alerte si la fréquence de résonance ou le temps de gain d'intensité/perte d'intensité dépasse ou viole des seuils respectifs. Le sous-système de surveillance de température comprend une sonde de température intégrée conçue pour surveiller la température de bobines individuelles et la température d'un connecteur de résonance magnétique/radiofréquence, ainsi qu'un processeur configuré pour émettre une alerte si l'une ou l'autre température dépasse un seuil.
PCT/US2023/063764 2022-03-11 2023-03-06 Technologies de surveillance pour bobines et réseaux d'irm WO2023172862A2 (fr)

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2023172862A3 (fr) * 2022-03-11 2024-01-04 Nortech Systems, Inc. Technologies de surveillance pour bobines et réseaux d'irm
RU2821393C1 (ru) * 2023-12-08 2024-06-24 Федеральное государственное бюджетное образовательное учреждение высшего образования "Московский государственный университет имени М.В. Ломоносова" (МГУ) Способ визуализации проводников катушки, используемой в магнитно-резонансной томографии (мрт)

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WO2023172862A3 (fr) * 2022-03-11 2024-01-04 Nortech Systems, Inc. Technologies de surveillance pour bobines et réseaux d'irm
RU2821393C1 (ru) * 2023-12-08 2024-06-24 Федеральное государственное бюджетное образовательное учреждение высшего образования "Московский государственный университет имени М.В. Ломоносова" (МГУ) Способ визуализации проводников катушки, используемой в магнитно-резонансной томографии (мрт)

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